Encapsulated heart valves

ABSTRACT

The present disclosure concerns embodiments of implantable prosthetic devices, and in particular, implantable prosthetic valves, and methods for making such devices. In one aspect, a prosthetic device includes encapsulating layers that extend over a fabric layer and secure the fabric layer to another component of the device. In particular embodiments, the prosthetic device comprises a prosthetic heart valve, and can be configured to be implanted in any of the native heart valves. In addition, the prosthetic heart valve can be, for example, a transcatheter heart valve, a surgical heart valve, or a minimally-invasive heart valve.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a divisional of U.S. patent application Ser. No.16/102,379, filed Aug. 13, 2018, now U.S. Pat. No. 10,543,080, which isa continuation of U.S. patent application Ser. No. 14/256,747, filedApr. 18, 2014, now U.S. Pat. No. 10,045,846, which is a divisional ofU.S. patent application Ser. No. 13/475,210, filed May 18, 2012, nowU.S. Pat. No. 8,945,209, which claims the benefit of U.S. PatentApplication No. 61/488,599, filed May 20, 2011, the entire disclosuresall of which are incorporated by reference for all purposes.

FIELD

The present disclosure relates to implantable prosthetic devices, andmore particularly, to valve prosthetics for implantation into bodyducts, such as native heart valve annuluses.

BACKGROUND

The human heart can suffer from various valvular diseases. Thesevalvular diseases can result in significant malfunctioning of the heartand ultimately require replacement of the native valve with anartificial valve. There are a number of known artificial valves and anumber of known methods of implanting these artificial valves in humans.

Artificial or prosthetic heart valves can be classified according to themanner in which they are implanted in the body. Implantation of surgicalvalves requires an open-chest surgery during which the heart is stoppedand the patient is placed on cardiopulmonary bypass. Transcatheter heartvalves can be delivered and deployed in the body by way ofcatheterization without opening the chest of the patient or employingcardiopulmonary bypass. Minimally-invasive heart valves generally referto valves that can be introduced into the body through a relativelysmall surgical incision yet still require the patient to be placed oncardiopulmonary bypass.

The various types of heart valves described above typically include arelatively rigid frame and a valvular structure, usually in the form offlexible valve leaflets, secured to the frame. The process forassembling a prosthetic valve is extremely labor intensive. For example,FIG. 1 illustrates a known transcatheter heart valve 10 that includes astent, or frame, 12, a valvular structure 14 comprising three leaflets16, and a fabric skirt 18 interposed between the frame 12 and thevalvular structure 14. To assemble the valve, the skirt 18 is manuallysutured to the bars of the frame using sutures 20, and then the valvularstructure is sutured to the skirt and the frame. The skirt assists inanchoring the valvular structure to the frame and sealing the valverelative to the native annulus so as to prevent paravalvular leakageonce implanted. As can be appreciated, the process for assembling thevalve is time consuming and requires significant manual labor. Thus, itwould be desirable to minimize the amount manual labor required toassemble a prosthetic valve.

SUMMARY

The present disclosure concerns embodiments of implantable prostheticdevices, and in particular, implantable prosthetic valves, and methodsfor making such devices. In one aspect, a prosthetic device includesencapsulating layers that extend over a fabric layer and secure thefabric layer to another component of the device. In particularembodiments, the prosthetic device comprises a prosthetic heart valve,and can be configured to be implanted in any of the native heart valves.In addition, the prosthetic heart valve can be, for example, atranscatheter heart valve, a surgical heart valve, or aminimally-invasive heart valve. The encapsulating layers desirably areformed from ePTFE or UHMWPE.

The encapsulating layers can be used to secure the fabric layer toanother component of the prosthetic device without using any sutures, orsubstantially minimizing the number of sutures needed to secure thefabric layer in place adjacent the other component of the prostheticdevice. In one example, inner and outer encapsulating layers can be usedto secure a fabric skirt to the annular frame of a transcatheter heartvalve, thereby replacing the need to manually sew the skirt to theframe, as currently done in the art.

This technique can also be used to secure fabric or cloth layers tovarious components of a surgical or minimally-invasive heart valve. Forexample, one or more of the sewing ring, wireform and stent assembly ofa surgical or minimally-invasive heart valve typically can be covered bya cloth cover. In some valves, a single cloth cover is used to cover oneor more of these components. The conventional method for assembling acloth cover around one or more components of a surgical orminimally-invasive heart valve involves manually sewing the longitudinaledges of the cloth cover to each other to form a covering around thevalve component. The disclosed technique can be used to secure a clothcovering around one or more components of a surgical orminimally-invasive heart valve in order to eliminate most or all of themanual sewing that usually is required.

In other embodiments, encapsulating layers, such as one or more layersof ePTFE or UHMWPE, can be applied to the frame of a prosthetic valvewithout a separate fabric layer. For example, in the case of aprosthetic valve having an expandable frame, one or more layers of ePTFEor UHMWPE can be applied to the frame (usually to the inside and outsideof the frame) without a separate fabric layer to facilitate tissuein-growth and to help seal the valve against surrounding tissue.

In one representative embodiment, an implantable prosthetic valvecomprises a valve component, a fabric layer disposed adjacent the valvecomponent, and a non-absorbable encapsulating material at leastpartially encapsulating the fabric layer and the valve component so asto secure the fabric layer to the valve component. The encapsulatingmaterial has a porous microstructure that promotes ingrowth ofsurrounding tissue to assist in securing the prosthetic valve in a bodylumen.

In another representative embodiment, an implantable prosthetic valvecomprises a radially collapsible and expandable annular frame. The framehas an inlet end and outlet end, and a plurality of frame membersdefining a plurality of gaps between the frame members. The valvefurther comprises an annular fabric skirt positioned adjacent the frameand configured to prevent blood from flowing through gaps in the framethat are covered by the skirt. An inner tubular layer is positioned onthe inside of the frame and the skirt, and an outer tubular layer ispositioned on the outside of the frame and the skirt. The inner andouter layers are bonded to each other at selected areas so as to form acovering that at least partially encapsulates the frame and skirt. Inaddition, one or more flexible valve leaflets can be sutured to theframe and the skirt.

In another representative embodiment, a method for making an implantableprosthetic device, comprises placing a first tubular covering member ona support; placing a subassembly of the prosthetic device over the firstcovering member, the subassembly comprising an annular component and afabric layer at least partially covering the annular component; placinga second tubular covering member over the subassembly; applying pressureto force the second covering member and the first covering member intocontact with other; and heating the first and second covering member toform a monolithic covering that at least partially encapsulates thesubassembly and thereby secures the fabric layer to the annularcomponent.

The foregoing and other features and advantages of the invention willbecome more apparent from the following detailed description, whichproceeds with reference to the accompanying figures.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a perspective view of a prior art prosthetic transcatheterheart valve.

FIG. 2 is a perspective view of prosthetic transcatheter heart valve,according to one embodiment.

FIG. 3 is a cross-section view of the heart valve of FIG. 2 taken alongline 3-3.

FIG. 4 is a perspective view of the frame of the heart valve of FIG. 2.

FIGS. 5A-5D illustrates a method for securing a fabric skirt to theframe of a heart valve by encapsulating the skirt and the frame.

FIG. 6 is a flow chart illustrating a method of constructing the heartvalve shown in FIG. 2, according to one embodiment.

FIG. 7 is a perspective view of a surgical heart valve, according toanother embodiment.

FIG. 8 shows the wireform of the valve of FIG. 7 and a cloth covering inthe process of being wrapped around the wireform.

FIG. 9 is a perspective view of a completed cloth-covered wireformassembly of the heart valve of FIG. 7.

FIG. 10 is a cross-sectional view of the wireform assembly of FIG. 9taken along line 10-10.

FIG. 11 is a perspective view of a cloth-covered sewing ring assembly ofthe heart valve of FIG. 7.

FIG. 12 is a cross-sectional view of the sewing ring assembly of FIG. 11taken along line 12-12.

FIG. 13 includes an exploded view and an assembled view of the stentassembly of the heart valve of FIG. 7.

FIG. 14 is a cross-sectional view of the stent assembly of FIG. 13 takenalong line 14-14.

FIG. 15 is a perspective view of the stent assembly.

FIG. 16 is an exploded view of the valve of FIG. 7 showing the assemblyof the wireform assembly, the stent assembly and the sewing ringassembly.

FIG. 17 is a perspective view of the heart valve of FIG. 7 shownpartially in section.

FIG. 18 is a perspective view of a heart valve, according to anotherembodiment.

DETAILED DESCRIPTION

As used in this application and in the claims, the singular forms “a,”“an,” and “the” include the plural forms unless the context clearlydictates otherwise. Additionally, the term “includes” means “comprises.”Although the operations of exemplary embodiments of the disclosed methodmay be described in a particular, sequential order for convenientpresentation, it should be understood that the disclosed embodiments canencompass an order of operations other than the particular, sequentialorder disclosed. For example, operations described sequentially may insome cases be rearranged or performed concurrently. Further,descriptions and disclosures provided in association with one particularembodiment are not limited to that embodiment, and may be applied to anyembodiment disclosed herein. Moreover, for the sake of simplicity, theattached figures may not show the various ways in which the disclosedsystem, method, and apparatus can be used in combination with othersystems, methods, and apparatuses.

The present disclosure concerns embodiments of implantable prostheticdevices, and in particular, implantable prosthetic valves, and methodsfor making such devices. In one aspect, a prosthetic device includesencapsulating layers that extend over a fabric layer and secure thefabric layer to another component of the device. In particularembodiments, the prosthetic device comprises a prosthetic heart valve,and can be configured to be implanted in any of the native heart valves.In addition, the prosthetic heart valve can be, for example, atranscatheter heart valve, a surgical heart valve, or aminimally-invasive heart valve. The prosthetic valve also can compriseother types of valves implantable within other body lumens outside ofthe heart or heart valves that are implantable within the heart atlocations other than the native valves, such as trans-atrial ortrans-ventricle septum valves.

FIG. 2 is an example of a transcatheter heart valve 50, according to oneembodiment. Valve 50 in the illustrated embodiment generally comprises aframe, or stent, 52, a leaflet structure 54 supported by the frame, anda skirt 56 secured to the outer surface of the leaflet structure. Valve50 typically is implanted in the annulus of the native aortic valve butalso can be adapted to be implanted in other native valves of the heartor in various other ducts or orifices of the body. Valve 50 has a“lower” end 80 and an “upper” end 82. In the context of the presentapplication, the terms “lower” and “upper” are used interchangeably withthe terms “inflow” and “outflow”, respectively. Thus, for example, thelower end 80 of the valve is its inflow end and the upper end 82 of thevalve is its outflow end.

Valve 50 and frame 52 are configured to be radially collapsible to acollapsed or crimped state for introduction into the body on a deliverycatheter and radially expandable to an expanded state for implanting thevalve at a desired location in the body (e.g., the native aortic valve).Frame 52 can be made of a plastically-expandable material that permitscrimping of the valve to a smaller profile for delivery and expansion ofthe valve using an expansion device such as the balloon of a ballooncatheter. Exemplary plastically-expandable materials that can be used toform the frame are described below. Alternatively, valve 50 can be aso-called self-expanding valve wherein the frame is made of aself-expanding material such as Nitinol, NiTiCo, NiTiCr, or alloys orcombinations thereof. A self-expanding valve can be crimped to a smallerprofile and held in the crimped state with a restraining device such asa sheath covering the valve. When the valve is positioned at or near thetarget site, the restraining device is removed to allow the valve toself-expand to its expanded, functional size.

Referring also to FIG. 4 (which shows the frame alone for purposes ofillustration), frame 52 is an annular, stent-like structure having aplurality of angularly spaced, vertically extending, commissureattachment posts, or struts, 58. Posts 58 can be interconnected via alower row 60 a of circumferentially extending struts 62 and first andsecond rows upper rows 60 b, 60 c, respectively, of circumferentiallyextending struts 64 and 66, respectively. The struts in each rowdesirably are arranged in a zig-zag or generally saw-tooth like patternextending in the direction of the circumference of the frame as shown.Adjacent struts in the same row can be interconnected to one another asshown in FIGS. 1 and 4 to form an angle A, which desirably is betweenabout 90 and 110 degrees, with about 100 degrees being a specificexample. The selection of angle A between approximately 90 and 110degrees optimizes the radial strength of frame 52 when expanded yetstill permits the frame 52 to be evenly crimped and then expanded in themanner described below.

In the illustrated embodiment, pairs of adjacent circumferential strutsin the same row are connected to each other by a respective, generallyU-shaped crown structure, or crown portion, 68. Crown structures 68 eachinclude a horizontal portion extending between and connecting theadjacent ends of the struts such that a gap 70 is defined between theadjacent ends and the crown structure connects the adjacent ends at alocation offset from the strut's natural point of intersection. Crownstructures 68 significantly reduce residual strains on the frame 52 atthe location of struts 62, 64, 66 during crimping and expanding of theframe 52 in the manner described below. Each pair of struts 64 connectedat a common crown structure 68 forms a cell with an adjacent pair ofstruts 66 in the row above. Each cell can be connected to an adjacentcell at a node 72. Each node 72 can be interconnected with the lower rowof struts by a respective vertical (axial) strut 74 that is connected toand extends between a respective node 72 and a location on the lower rowof struts 62 where two struts are connected at their ends opposite crownstructures 68.

In certain embodiments, lower struts 62 have a greater thickness ordiameter than upper struts 64, 66. In one implementation, for example,lower struts 62 have a thickness of about 0.42 mm and upper struts 64,66 have a thickness of about 0.38 mm. Because there is only one row oflower struts 62 and two rows of upper struts 64, 66 in the illustratedconfiguration, enlargement of lower struts 62 with respect to upperstruts 64, 66 enhances the radial strength of the frame at the lowerarea of the frame and allows for more uniform expansion of the frame.

Suitable plastically-expandable materials that can be used to form theframe include, without limitation, stainless steel, cobalt, chromium,titanium, nickel, or alloys or combinations thereof (e.g., anickel-cobalt-chromium alloy). Some embodiments can comprise a flexiblebiocompatible polymer, such as polypropylene, polyurethanes or silicon.In particular embodiments, frame 52 is made of anickel-cobalt-chromium-molybdenum alloy, such as MP35N™ (tradename ofSPS Technologies), which is equivalent to UNS R30035 (covered by ASTMF562-02). MP35N™/UNS R30035 comprises 35% nickel, 35% cobalt, 20%chromium, and 10% molybdenum, by weight. It has been found that the useof MP35N to form frame 52 provides superior structural results overstainless steel. In particular, when MP35N is used as the framematerial, less material is needed to achieve the same or betterperformance in radial and crush force resistance, fatigue resistances,and corrosion resistance. Moreover, since less material is required, thecrimped profile of the frame can be reduced, thereby providing a lowerprofile valve assembly for percutaneous delivery to the treatmentlocation in the body.

Leaflet structure 54 can comprise three leaflets 76, which can bearranged to collapse in a tricuspid arrangement, as best shown in FIG.2. Lower edge 88 of leaflet structure 54 desirably has an undulating,curved scalloped shape. By forming the leaflets with this scallopedgeometry, stresses on the leaflets are reduced, which in turn improvesdurability of the valve. Moreover, by virtue of the scalloped shape,folds and ripples at the belly of each leaflet (the central region ofeach leaflet), which can cause early calcification in those areas, canbe eliminated or at least minimized. The scalloped geometry also reducesthe amount of tissue material used to form leaflet structure, therebyallowing a smaller, more even crimped profile at the inflow end of thevalve. The leaflets 76 can be formed of bovine pericardial tissue,biocompatible synthetic materials, or various other suitable natural orsynthetic materials as known in the art and described in U.S. Pat. No.6,730,118, which is incorporated by reference herein.

The skirt 56 can be formed, for example, of polyethylene terephthalate(PET) ribbon or polyester fabric (e.g., Dacron). The thickness of theskirt can vary, but is desirably less than 6 mil, and desirably lessthan 4 mil, and even more desirably about 2 mil. Traditionally, fabricskirts have been secured to frames using sutures, as illustrated inFIG. 1. In contrast, in the illustrated embodiment, skirt 56 desirablyis secured to frame 52 without sutures and instead is secured to frame52 with inner and outer encapsulating layers 84, and 86, respectively(FIG. 3). The encapsulating layers 84, 86 are fused, bonded, orotherwise secured to each other through the openings in the frame 52,which effectively encapsulates the frame 52 and the skirt 56 to securethese components in their assembled state shown in FIG. 2.

The skirt 56 of the prosthetic valve can serve several functions. Inparticular embodiments, for example, the skirt primarily functions toanchor the leaflet structure to the frame. In addition, the skirt 56, incooperation with the encapsulating layers 84, 86, help prevent (ordecrease) perivalvular leakage.

In the illustrated embodiment, each of the inner and outer layers 84, 86extend the axial length of the frame 52 (from the lower end 80 to theupper end 82), and therefore completely encapsulates or substantiallyencapsulates the entire frame 52 and skirt 56. In alternativeembodiments, the layers 84, 86 can be shorter than the axial length ofthe frame 52 and/or the skirt 56 such that the layers 84, 86 onlyencapsulate selected portions of the frame and the skirt. Although inthe illustrated embodiment the layers 84, 86 are tubular or cylindricalin shape, the inner and outer layers 84, 86 need not extend along theinner and outer surfaces of the frame in the circumferential directionthrough 360 degrees. In other words, the inner and outer layers 84, 86can have a cross-sectional profile (in a plane perpendicular to the axisof the lumen of the valve) that is not a complete circle.

The encapsulating layers 84, 86 desirably are made of a non-absorbablepolymeric material (i.e., a material that does not dissolve onceimplanted in the body). Examples of such materials include withoutlimitation, expanded polytetrafluoroethylene (ePTFE), unexpanded porousPTFE, woven polyester or expanded PTFE yarns, PTFE, ultrahigh molecularweight polyethylene (UHMWPE), other polyolefins, composite materialssuch as ePTFE with PTFE fibers, or UHMWPE film with embedded UHMWPEfibers, polyimides, silicones, polyurethane, hydrogels,fluoroethylpolypropylene (FEP), polypropylfluorinated amines (PFA),other related fluorinated polymers, or various combinations of any ofthese materials. In particular embodiments, the encapsulating layers 84,86 are formed from respective tubes made of a suitable polymericmaterial (e.g., ePTFE tubes or UHMWPE tubes) that are bonded to eachother when subjected to heat treatment, as described in detail below.

Microporous expanded polytetrafluoroethylene (ePTFE) tubes can be madeby of a number of well-known methods. Expanded PTFE is frequentlyproduced by admixing particulate dry polytetrafluoroethylene resin witha liquid lubricant to form a viscous slurry. The mixture can be pouredinto a mold, typically a cylindrical mold, and compressed to form acylindrical billet. The billet can then be ram extruded through anextrusion die into either tubular or sheet structures, termed extrudatesin the art. The extrudates comprise an extruded PTFE-lubricant mixturecalled “wet PTFE.” Wet PTFE has a microstructure of coalesced, coherentPTFE resin particles in a highly crystalline state. Following extrusion,the wet PTFE can be heated to a temperature below the flash point of thelubricant to volatilize a major fraction of the lubricant from the PTFEextrudate. The resulting PTFE extrudate without a major fraction oflubricant is known in the art as dried PTFE. The dried PTFE can then beeither uniaxially, biaxially or radially expanded using appropriatemechanical apparatus known in the art. Expansion is typically carriedout at an elevated temperature, e.g., above room temperature but below327 degrees C., the crystalline melt point of PTFE. Uniaxial, biaxial orradial expansion of the dried PTFE causes the coalesced, coherent PTFEresin to form fibrils emanating from nodes (regions of coalesced PTFE),with the fibrils oriented parallel to the axis of expansion. Onceexpanded, the dried PTFE is referred to as expanded PTFE (“ePTFE”) ormicroporous PTFE.

UHMWPE is made up of very long chains of polyethylene, with molecularweight numbering in the millions, usually between 2 and 6 million. It ishighly resistant to corrosive chemicals, has extremely low moistureabsorption and a very low coefficient of friction. It isself-lubricating and highly resistant to abrasion. UHMWPE is processedusing compression molding, ram extrusion, gel spinning, and sintering.UHMWPE is available commercially as a powder, in sheets or rods, and asfibers.

Referring now to FIGS. 5A-5D and 6, an exemplary method for forming thevalve 50 will now be described. Although the use of ePTFE is describedbelow, it is merely exemplary in nature and is not intended as alimitation. It is to be understood that other materials such as UHMWPE,composite materials, or any other non-absorbable polymeric materialdescribed above can be used.

First, as depicted in FIG. 5A, an inner layer 84 comprising an ePTFEtube can be placed on a mandrel 100. Second, as depicted in FIG. 5B, aframe 52 can be placed over the inner layer 84. Third, as depicted inFIG. 5C, the skirt 56 can be placed over the frame 52. The skirt 56 canbe in the form of a sheet of material that is tightly wrapped around theouter surface of the frame. Layers of PTFE tape 90 can be wrapped aroundthe opposite ends of the skirt and the frame to temporarily secure thelocation and placement of the skirt on the frame. Fourth, as depicted inFIG. 5D, an outer layer 86 comprising an ePTFE tube can be placed overthe skirt 56. After the outer layer is in position, the temporary tapelayers 90 can be removed. The tape layers 90 help maintain the locationof the skirt relative to the frame and the location of the skirt and theframe relative to the mandrel as the outer layer 86 is slid over themandrel and over the skirt and the frame. As further shown in FIG. 5D,further layers of PTFE tape 92 can now be wrapped around the ends of theouter layer 86 to help secure the position of the outer layer to theunderlying layers of the assembly and to the mandrel during subsequentprocessing.

An alternative way to encapsulate the frame with polymer is by using theelectrospinning technique. Electrospinning uses an electrical charge todraw very fine (typically on the micro or nano scale) fibers from aliquid.

The assembly shown in FIG. 5D can now undergo an encapsulation processwhereby the assembly is subjected to heat and/or pressure to cause theinner and outer layers to bond to each other through the openings in theframe 52 and at the ends of the tubular layers that extend beyond theopposite ends of the frame 52 to encapsulate the frame and the skirtbetween the inner and outer layers. During this step, the entire outersurface of the assembly on the mandrel can be tightly wrapped with asuitable material (e.g., PTFE tape) to apply pressure to the variouslayers of the assembly. The entire assembly, including the mandrel, canbe transferred to an oven where the inner and outer layers 84, 86 aresintered by being heated to a predetermined temperature. In oneimplementation, for example, the inner and outer layers are sintered bybeing heated to a temperature above 327 degrees C., the crystalline meltpoint of PTFE.

During the sintering process the ePTFE is restrained against uniaxial,biaxial or radial contraction. Sintering causes at least a portion ofthe crystalline PTFE to change from a crystalline state to an amorphousstate. The conversion from a highly crystalline structure to one havingan increased amorphous content locks the node and fibril microstructure,as well as its orientation relative to the axis of expansion, andprovides a dimensionally stable tubular or sheet material upon cooling.

After the sintering process, the assembly is removed from the oven andallowed to cool. The material wrapped around the assembly, as well astape layers 92, can now be removed. The portions of the inner and outerlayers 84, 86 that extend beyond the opposite ends of the stent 52 canbe trimmed so that the inner and outer layers 84, 86 are the same lengthor substantially the same length as the frame 52. In this manner, theframe 52 can be completely covered or substantially covered by layers84, 86. If desired, selected portions of the inner and outer layers 84,86 can be removed to facilitate crimping of the valve for delivery intoa patient. Suitable techniques and mechanisms can be used to selectivelyremove portions of layers 84, 86, such as laser cutting. For example,portions of the inner and outer layers 84, 86 that cover the openings inthe frame 52 can be cut or otherwise removed to minimize the amount ofmaterial in the valve, which can facilitate crimping of the valve to arelatively small diameter. In particular embodiments, the portions oflayers 84, 86 extending from the upper edge of the skirt 56 to the upperedge of the frame can be completely removed to expose the struts of theframe that extend above the upper edge of the skirt.

In an alternative embodiment, the skirt 56 can be preformed in a tubularor cylindrical configuration. In this embodiment, the skirt can bepositioned on the frame 52 by first partially crimping the frame to adiameter smaller than the diameter of the skirt. The skirt is thenplaced over the partially crimped frame and then the frame is expandedback to its functional size. The skirt desirably is sized such that theexpanded frame applies at least some outward radial pressure against theskirt to assist in retaining the skirt on the frame. The frame and skirtassembly can then be loaded onto inner layer 84 (already on themandrel), and encapsulated following the process described above. Inanother embodiment, the skirt 56 can be placed on the inside of theframe 52. For example, the skirt 56 can be in the form of a sheet ofmaterial that is wrapped around inner layer 84 prior to placing theframe on the mandrel, or it can have a tubular configuration that isslid onto inner layer 84 prior to placing the frame on the mandrel.

Leaflet structure 54 can be attached to the skirt 56 and/or the frame 52using sutures or other suitable techniques or mechanisms. In theillustrated embodiment shown in FIG. 2, for example, each leaflet 76 hasa tab 102 that is sutured to an adjacent tab of another leaflet to forma commissure of the leaflet structure. Each commissure can be secured toa commissure post 58 of the frame 52, such as with sutures 106 thatextend through the leaflet tabs 102 and apertures in the commissureposts 58 of the frame. The lower, or inflow, end portion of the leaflets76 can be sutured directly to the skirt 56 along a suture line 108 thattracks the curvature of the scalloped lower edge 88 of the leafletstructure. Any suitable suture, such as an Ethibond suture, can be usedto secure the leaflets to the skirt along suture line 108.

In certain embodiments, the lower edges of the leaflets can be securedto the skirt 56 via a thin PET reinforcing strip (not shown), asdisclosed in co-pending U.S. Pat. No. 7,993,394, which is incorporatedherein by reference. As described in U.S. Pat. No. 7,993,394, thereinforcing strip can be sutured to the lower edges of the leaflets. Thereinforcing strip and the lower edges of the leaflets can then besutured to the skirt 56 along suture line 108. The reinforcing stripdesirably is secured to the inner surfaces of the leaflets 76 such thatthe lower edges of the leaflets become sandwiched between thereinforcing strip and the skirt 56 when the leaflets and the reinforcingstrip are secured to the skirt. The reinforcing strip enables a securesuturing and protects the pericardial tissue of the leaflet structurefrom tears.

As noted above, the conventional method for securing a skirt to a frameinvolves manually suturing the skirt to the frame. In contrast, theillustrated embodiment relies on the inner and outer layers 84, 86 tosecure the skirt 56 in place relative to the frame. As can beappreciated, this technique for securing the skirt to the frame cansignificantly reduce the amount of labor required to assemble a valve.The use of layers 84, 86 provides other advantages as well. For example,the outer layer 86, when formed from ePTFE or UHMWPE, has a porousmicrostructure that facilitates tissue in-growth from surrounding tissueafter the valve is implanted.

In addition, inner and outer layers 84, 86 can protect the leaflets 76during crimping and facilitate even and predictable crimping of thevalve. When a prosthetic valve is placed in a crimping apparatus toradial compress the valve to a smaller diameter for insertion into apatient, the leaflets of the valve are pressed against the inner surfaceof the metal frame and portions of the tissue can protrude into the opencells of the frame between the struts and can be pinched due to thescissor-like motion of the struts of the frame. If the valve is severelycrimped to achieve a small crimping size, this scissor-like motion canresult in cuts and rupture of the tissue leaflets. To protect theleaflets during crimping, it is known to place a deformable materialaround the valve to prevent direct contact between the hard surface ofthe jaws of the crimping apparatus and the valve. The deformablematerial can protrude into the open cells, thereby preventing theleaflets from entering this space and being pinched by metal struts ofthe frame. Layers 84, 86 function in a manner similar to this deformablematerial to protect leaflets from being pinched during crimping. Assuch, the disclosed valve 50 can be placed in a crimping apparatuswithout an additional protective layer of material surrounding thevalve. Due to the presence of layers 84, 86, the valve 50 can be crimpedonto the balloon of a balloon catheter in an even and predictable mannerthat forms a very ordered structure of balloon-leaflets-frame (frominward to outward). Additionally, inner layer 84 can prevent directcontact between the leaflets 76 and the frame during working cycles ofthe valve (i.e., as the valve leaflets open and close in response toblood pressure) to protect the leaflets against damage caused by contactwith the frame.

Moreover, as noted above, the skirt 56 can be a fabric, such as a PETcloth. PET or other fabrics are substantially non-elastic (i.e.,substantially non-stretchable and non-compressible). As such, in knownprosthetic valves, the skirt can wrinkle after expansion from thecrimped diameter. In the illustrated embodiment, the skirt 56 can betightly compressed against the frame by layers 84, 86 such that when thevalve is expanded to its functional size from the crimped state, theskirt can recover to its original, smooth surfaces with little or nowrinkling.

The encapsulation process described above in the context of securing askirt to the frame of an expandable transcatheter heart valve. The skirttypically is more durable than the ePTFE layers and therefore the skirtreinforces the ePTFE layers where they undergo stresses from cyclicloading of the valve. However, in alternative embodiments, the valve canbe formed without the skirt 56 to permit crimping of the valve to asmaller delivery diameter. In such embodiments, the ePTFE layers 84, 86serve as the primary sealing mechanism that prevents paravalvularleakage through the frame of the valve. In other embodiments, the skirt56 can be used to reinforce only selected portions of the layers 84, 86,such as those portions of layers 84, 86 subject to greatest loading,while the remaining portions of layers 84, 86 do not contain a fabriclayer or skirt.

It should be noted that the encapsulation process can be utilized tosecure a fabric or woven textile element to other components of aprosthetic valve. For example, surgical valves (valves which aretypically implanted via open-heart surgery) include several componentsthat are covered with a cloth or fabric material. Known surgical valvestypically have a sewing ring and one or more stent components, each ofwhich are covered with a cloth member. The cloth member typically iswrapped around the valve component and the longitudinal edges of thecloth member are manually stitched to each other to secure the clothmember around the valve component. As can be appreciated, this is atedious and time-consuming process.

Accordingly, another embodiment of the present disclosure utilizes theencapsulation process described herein to secure cloth members aroundcomponents of a surgical valve to reduce the amount of the manual laborrequired to assemble the valve. FIG. 7 shows a surgical valve 200,according to one embodiment, that includes multiple components that areformed by the encapsulation process. The valve 200 generally includes awireform assembly 202 (as best shown in FIGS. 8-10), a sewing ringassembly 204 (as best shown in FIGS. 11-12), a stent assembly 206 (asbest shown in FIGS. 13-15), and a valvular structure 208 (as best shownin FIG. 7). The valvular structure 208 can comprises three leaflets 210arranged in a tricuspid arrangement as known in the art.

Referring to FIGS. 8-10, the wireform assembly 202 comprises a wireform212, a cloth cover 214 and encapsulating layers 216, 218. As usedherein, the term “wireform” refers generally to a portion of aprosthetic heart valve that provides support for the leaflets of thevalve. The wireform typically is formed from one or more pieces of wirebut also can be formed from other similarly-shaped elongate members. Thewireform can also be cut or otherwise formed from tubing or a sheet ofmaterial. The wireform can have any of various cross sectional shapes,such as a square, rectangular, or circle (as shown in FIG. 10), orcombinations thereof. In particular embodiments, the wireform 212 ismade of a relatively rigid metal, such as stainless steel or Elgiloy (aCo—Cr—Ni alloy).

FIG. 8 shows the wireform 212 partially covered by the cloth cover 214.The cloth cover can be formed of any biocompatible fabric, such as, forexample, polyethylene terephthalate. The cloth cover 214 comprises anelongated strip of material having opposing ends that are broughttogether to form a butt joint in the manner shown in FIG. 8. Theopposing longitudinal edges 220, 222 of the cloth cover are then wrappedaround the wireform 212. It is known to stitch together the longitudinaledges of the cloth covering along its entire length, which istime-consuming process. Instead, in the illustrated embodiment, thecloth cover is secured around the wireform 212 by the encapsulatinglayers 216, 218.

The encapsulating layers can be formed in a process similar to thatdescribed above for securing encapsulating layers 84, 86 around frame 52and skirt 56. In one specific approach, for example, a first ePTFE tube,which forms layer 216, can be placed on a mandrel. The first ePTFE tubecan have a diameter that is slightly smaller than the diameter of thewireform 212 and an axial length that is slightly greater than the axiallength of the wireform 212. The cloth covered wireform can then beplaced over the first ePTFE tube. A second ePTFE tube, which forms layer218 is then placed over the cloth covered wireform. The second ePTFEtube can have a diameter and axial length that are slightly greater thanthat of the wireform 212. To help retain the cloth cover 214 wrappedaround the wireform 212 during the previous steps, the longitudinaledges 220, 222 can be stitched together at a few selected locationsalong the length of the cloth cover. The entire assembly can then bewrapped with a suitable material and then placed in an oven to sinterthe ePTFE tubes. After sintering, the wrapping material is removed. Thefirst and second ePTFE tubes can have a length that is slightly greaterthan the axial length of the wireform. In this manner, the entireassembly forms a tubular body completely encapsulating the wireform.Excess ePTFE material can be cut away to form layers 216, 218 thattogether form a covering that closely conforms to the shape of thewireform 212, as depicted in FIG. 10.

Referring to FIGS. 11 and 12, the sewing ring assembly 204 comprises asewing ring insert 226, a cloth cover 228, and encapsulating layers 230,232. The sewing ring insert 226 can have a conventional construction andcan be made of a suture permeable material for suturing the valve to anative annulus, as known in the art. For example, the sewing ring insert226 can be made of a silicone-based material, although othersuture-permeable materials can be used. The cloth cover 228 can beformed of any biocompatible fabric, such as, for example, polyethyleneterephthalate. As with the wireform assembly, it is known to stitchtogether the edges of the cloth covering of the sewing ring along itslength, which is a time-consuming process. Instead, in the illustratedembodiment, the cloth covering 228 can be secured around the sewing ringinsert by the encapsulating layers 230, 232.

The encapsulating layers can be formed in a process similar to thatdescribed above for securing encapsulating layers 84, 86 around frame 52and skirt 56. In one specific approach, for example, a first ePTFE tube,which forms layer 230, can be placed on a mandrel. The first ePTFE tubecan have a diameter that is slightly smaller than the diameter of thesewing ring insert 226 and an axial length that is slightly greater thanthe axial length of the sewing ring insert. The cloth covered sewingring insert can then be placed over the first ePTFE tube. The mandrelcan have a tapered or substantially conical surface portion that isshaped to support the sewing insert. A second ePTFE tube, which formslayer 232 is then placed over the cloth covered sewing ring insert. Thesecond ePTFE tube can have a diameter and axial length that are slightlygreater than that of the sewing ring insert. To help retain the clothcover 228 wrapped around the sewing ring insert during the previoussteps, the longitudinal edges 234, 236 can be stitched together at a fewselected locations along the length of the cloth cover. The entireassembly can then be wrapped with a suitable material and then placed inan oven to sinter the ePTFE tubes. After sintering, the wrappingmaterial is removed. The first and second ePTFE tubes can have a lengththat is slightly greater than the axial length of the sewing ringassembly. In this manner, the entire assembly forms an annular bodycompletely encapsulating the sewing ring and cloth cover. Excess ePTFEmaterial can be cut away to form layers 230, 232 that together form acovering that closely conforms to the shape of the sewing ring insert,as depicted in FIG. 12.

Referring to FIGS. 13 and 14, the stent, or band, assembly 206 cancomprise an inner support 240 and an outer band 242 disposed around theinner support 240. The inner support 240 can comprise cusp portions 244extending between upstanding commissure portions 246. The outer band 242can be shaped to conform to the curvature of the cusp portions of theinner support. The inner support 240 desirably is made of a polymericmaterial, such as polyester, although materials, including metals andother polymeric materials can be used. The outer band desirably is madeof a relatively rigid metal, such as Elgiloy (a Co—Cr—Ni alloy) orstainless steel. As best shown in FIG. 14, a cloth cover 248 in theillustrated embodiment completely covers the inner support 240 and theouter band 242. Encapsulating layers 250, 252 encapsulate the clothcover 248. As with the wireform assembly, it is known to stitch togetherthe edges of the cloth covering of the stent assembly along its length,which is a time-consuming process. Instead, in the illustratedembodiment, the cloth covering 248 can be secured around the innersupport and outer band by the encapsulating layers 250, 252.

The encapsulating layers can be formed in a process similar to thatdescribed above for securing encapsulating layers 84, 86 around frame 52and skirt 56. In one specific approach, for example, a first ePTFE tube,which forms layer 250, can be placed on a mandrel. The first ePTFE tubecan have a diameter that is slightly smaller than the diameter of theinner support 240 and an axial length that is slightly greater than theaxial length of the inner support 240. The cloth covered stent assembly(i.e., the inner support 240, outer band 242, and cloth cover 248) canthen be placed over the first ePTFE tube. A second ePTFE tube, whichforms layer 252 is then placed over the cloth covered wireform. Thesecond ePTFE tube can have a diameter and axial length that are slightlygreater than that of the inner support 240. To help retain the clothcover 248 wrapped around the inner support 240 and the outer band 242during the previous steps, the longitudinal edges 254, 256 can bestitched together at a few selected locations along the length of thecloth cover. The entire assembly can then be wrapped with a suitablematerial and then placed in an oven to sinter the ePTFE tubes. Aftersintering, the wrapping material is removed. The first and second ePTFEtubes can have a length that is slightly greater than the axial lengthof the wireform. In this manner, the entire assembly forms a tubularbody completely encapsulating the wireform. Excess ePTFE material can becut away to form layers 250, 252 that together form a covering thatclosely conforms to the shape of the cloth covered stent assembly.

Once the wireform assembly 202, sewing ring assembly 204, and stentassembly 206 are formed, these components can be assembled together withleaflets 210 to form the assembled valve. These components can beassembled in a conventional manner. As shown in FIG. 16, for example,three leaflets 210 can be positioned with the wireform assembly 202.Each leaflet 210 can include two tabs 260 positioned on opposing ends ofthe leaflet. Each respective tab 260 can be aligned with a tab 260 of anadjacent leaflet as shown. The lower edge of each leaflet extendingbetween the tabs 260 can be sutured to the cloth covering 214 of thewireform assembly 202. Each pair of aligned tabs 260 can be insertedbetween adjacent upright extensions 264 of the wireform assembly 202.The tabs 260 can then be wrapped around a respective commissure support266 of the stent assembly 206 (as best shown in FIG. 17). The tabs 260can be sutured or otherwise coupled to each other and/or to thecommissure post 266.

The wireform assembly 202 can be then be secured to an upper innerportion of the stent assembly 206 and the sewing ring assembly 204 canbe secured to a lower outer portion of the stent assembly 206. The stentassembly 204 can matingly engage a corresponding contour of the wireformassembly. Thus, the commissure posts 266 and the cusp portions extendingbetween the commissure posts can be sized and shaped so as to correspondto the curvature of the wireform assembly. The wireform assembly 202 canbe secured to the stent assembly 206 via sutures extending through thecloth covering of the wireform assembly and the apertures in the innersupport 240 and outer band 242 (FIG. 13) of the stent assembly. Thesewing ring assembly 204 can be secured to the stent assembly viasutures extending through the sewing ring assembly and the apertures inthe inner support 240 and outer band 242 (FIG. 13) of the stentassembly. Cloth covers 262 (FIG. 16) can be positioned over the exposedportions of the tabs 260 of the leaflets, and secured in place withsutures. The covers 262 can be formed from any biocompatible fabric orpolymer.

FIG. 18 shows an embodiment of a heart valve 300, according to anotherembodiment. The heart valve can be implanted in the heart (e.g., in theaortic annulus, as shown in FIG. 18) using conventional surgicaltechniques or a minimally-invasive technique. The heart valve 300includes a valve component 302 and an expandable frame component 304.The valve component 302 can be a conventional surgical valve having asewing ring 306. The frame component 304 can be secured to the sewingring using any of various connection techniques, such as suturing. Inthis embodiment, the frame component 304 can be deployed within a nativeheart valve annulus similar to a conventional transcatheter valve andtherefore serves as an anchor for the valve component. Similar valvescomprised of a surgical valve combined with an expandable frame andmethods for implanting such valves are disclosed in U.S. Pat. No.8,308,798 and U.S. Patent Publication No. 2012/0065729, which areincorporated herein by reference.

The valve 300 desirably comprises inner and outer layers 308 coveringthe inside and outside of the metal frame component 304. The layers 308can be formed from tubular ePTFE layers utilizing the techniquesdescribed above for securing encapsulating layers 84, 86 around frame52. However, the valve 300 in the illustrated embodiment does notinclude a separate cloth layer covering the frame component 304, whichin some applications may be needed to reinforce the ePTFE layers wherethey undergo significant stress from cyclic loading of the valve. Asshown in FIG. 18, the frame component 304 functions primarily to anchorthe valve within the native annulus. The ePTFE layers on the framecomponent facilitate ingrowth of tissue and provide perivalvular sealingbelow the sewing ring 306. Once implanted, most of the stress caused bycyclic loading of the valve is born by the valve component 302 andlittle, if any, cyclic loading is experienced by the frame component304. As such, the ePTFE layers 308 can provide adequate perivalvularsealing without a separate fabric layer reinforcing the ePTFE layers.

In alternative embodiments, the valve 300 can include a fabric layer(not shown) covering the inside and/or outside of the frame component304. The fabric layer can be secured to the frame component 304 usingthe ePTFE layers as described herein.

In view of the many possible embodiments to which the principles of thedisclosed invention may be applied, it should be recognized that theillustrated embodiments are only preferred examples of the invention andshould not be taken as limiting the scope of the invention. Rather, thescope of the invention is defined by the following claims. We thereforeclaim as our invention all that comes within the scope and spirit ofthese claims.

We claim:
 1. An encapsulated implantable prosthetic heart valve,comprising: a radially collapsible and expandable annular frame; afabric layer adjacent the annular frame to form a subassembly; a firsttubular covering member placed within the subassembly; a second tubularcovering member positioned over the subassembly and the first coveringmember so that the second covering member is coextensive with the firstcovering member, wherein the first and second tubular covering membersare fused together by heat and pressure to form a monolithic coveringthat at least partially encapsulates the subassembly to form anencapsulated annular frame; and valvular leaflets positioned within theencapsulated annular frame and sutured to the fabric layer, the valvularleaflets being configured to permit blood flow in a first directionthrough the heart valve and block blood flow through the heart valve ina second direction, opposite the first direction.
 2. The heart valve ofclaim 1, wherein the fabric layer comprises an annular skirt disposed onthe frame.
 3. The heart valve of claim 3, wherein the annular framecomprises a plurality of frame members defining a plurality of gapsbetween the frame members, and the annular skirt is configured toprevent blood from flowing through gaps in the frame that are covered bythe annular skirt.
 4. The heart valve of claim 3, wherein the annularskirt extends only partway along the annular frame from a first end to amidpoint thereof, and portions of the first and second covering membersbetween the midpoint and a second end of the annular frame are removedto facilitate crimping of the valve for subsequent delivery into apatient.
 5. The heart valve of claim 1, wherein the first and secondcovering members are substantially the same length as the frame.
 6. Theheart valve of claim 1, wherein the first and second covering membersare non-absorbable and have a porous microstructure that promotesingrowth of surrounding tissue to assist in securing the prostheticheart valve in a body lumen.
 7. The heart valve of claim 6, wherein thefirst and second tubular covering members comprise ePTFE or UHMWPE. 8.The heart valve of claim 7, wherein the fabric layer is a PET cloth andthe first and second covering members comprise ePTFE.
 9. The heart valveof claim 1, wherein the fabric layer is disposed on the outside of theframe.
 10. The heart valve of claim 9, wherein a second fabric layer isalso disposed on the inside of the frame.
 11. The heart valve of claim1, further including a reinforcing strip secured to inner surfaces oflower edges of each of the leaflets, sandwiching the lower edges betweenthe reinforcing strips and the fabric layer and suturing the lower edgesof the leaflets to the skirt.
 12. An encapsulated implantable prostheticheart valve, comprising: a radially collapsible and expandable annularframe partially crimped from an expanded size having a first diameter toa smaller partially crimped size having a second diameter; an annularfabric skirt positioned around the partially crimped frame, the skirtbeing formed in a tubular configuration having a skirt diameter smallerthan the first diameter; wherein the frame is expanded to an expandedsize such that the expanded frame applies outward radial pressureagainst the skirt to retain the skirt on the frame, the expanded frameand skirt retained thereon forming a sub assembly; a first tubularcovering member placed within the subassembly; a second tubular coveringmember positioned over the subassembly and the first covering member sothat the second tubular covering member at least partly covers thesubassembly and is coextensive with the first tubular covering member,wherein the first and second tubular covering members are fused togetherby heat and pressure to form a monolithic covering that at leastpartially encapsulates the subassembly to form an encapsulated annularframe; and valvular leaflets positioned within the encapsulated annularframe and sutured to the skirt, the valvular leaflets being configuredto permit blood flow in a first direction through the heart valve andblock blood flow through the heart valve in a second direction, oppositethe first direction.
 13. The heart valve of claim 12, wherein the firstand second tubular covering members are non-absorbable and have a porousmicrostructure that promotes ingrowth of surrounding tissue to assist insecuring the prosthetic heart valve in a body lumen.
 14. The heart valveof claim 11, wherein the first and second tubular covering memberscomprise ePTFE or UHMWPE.
 15. The heart valve of claim 14, wherein theskirt is a PET cloth and the first and second covering members compriseePTFE.
 16. The heart valve of claim 12, wherein the skirt is completelyencapsulated by the monolithic covering formed by the first and secondtubular covering members.
 17. The heart valve of claim 12, wherein theannular frame comprises a plurality of frame members defining aplurality of gaps between the frame members, and wherein the first andsecond tubular covering members are formed with gaps that correspond togaps in the frame that are not covered by the skirt.
 18. The heart valveof claim 12, wherein an inflow end of the skirt is aligned with aninflow end of the annular frame and a portion of the annular framebetween an outflow end of the skirt and an outflow end of the annularframe is not covered by the first and second tubular covering members.19. The heart valve of claim 12, wherein a second annular fabric skirtis also disposed on the inside of the frame.
 20. The heart valve ofclaim 12, wherein the radially collapsible and expandable tubular frameis formed of a material that is plastically expandable.
 21. The heartvalve of claim 12, wherein the radially collapsible and expandabletubular frame is formed of a material that is self-expandable.